Implantable medical devices fabricated from branched polymers

ABSTRACT

Stent scaffolds comprising branched biocompatible polymers are disclosed.

CROSS REFERENCE TO RELATED APPLICATION

This application is a continuation of application Ser. No. 13/941,374filed on 12 Jul. 2013, which application is a divisional of applicationSer. No. 11/784,886, filed Apr. 9, 2007 and issued as U.S. Pat. No.8,486,135 on 16 Jul. 2013, which patent claims the benefit ofProvisional Patent Application No. 60/810,302, filed Jun. 1, 2006. Allrelated applications and the patent are incorporated fully herein byreference.

BACKGROUND OF THE INVENTION

Field of the Invention

This invention relates to implantable medical devices fabricated frompolymer blends including branched polymers.

Description of the State of the Art

This invention relates to radially expandable endoprostheses, which areadapted to be implanted in a bodily lumen. An “endoprosthesis”corresponds to an artificial device that is placed inside the body. A“lumen” refers to a cavity of a tubular organ such as a blood vessel.

A stent is an example of such an endoprosthesis. Stents are generallycylindrically shaped devices, which function to hold open and sometimesexpand a segment of a blood vessel or other anatomical lumen such asurinary tracts and bile ducts. Stents are often used in the treatment ofatherosclerotic stenosis in blood vessels. “Stenosis” refers to anarrowing or constriction of the diameter of a bodily passage ororifice. In such treatments, stents reinforce body vessels and preventrestenosis following angioplasty in the vascular system. “Restenosis”refers to the reoccurrence of stenosis in a blood vessel or heart valveafter it has been treated (as by balloon angioplasty, stenting, orvalvuloplasty) with apparent success.

The treatment of a diseased site or lesion with a stent involves bothdelivery and deployment of the stent. “Delivery” refers to introducingand transporting the stent through a bodily lumen to a region, such as alesion, in a vessel that requires treatment. “Deployment” corresponds tothe expanding of the stent within the lumen at the treatment region.Delivery and deployment of a stent are accomplished by positioning thestent about one end of a catheter, inserting the end of the catheterthrough the skin into a bodily lumen, advancing the catheter in thebodily lumen to a desired treatment location, expanding the stent at thetreatment location, and removing the catheter from the lumen.

In the case of a balloon expandable stent, the stent is mounted about aballoon disposed on the catheter. Mounting the stent typically involvescompressing or crimping the stent onto the balloon. The stent is thenexpanded by inflating the balloon. The balloon may then be deflated andthe catheter withdrawn. In the case of a self-expanding stent, the stentmay be secured to the catheter via a constraining member such as aretractable sheath or a sock. When the stent is in a desired bodilylocation, the sheath may be withdrawn which allows the stent toself-expand.

The stent must be able to satisfy a number of mechanical requirements.First, the stent must be capable of withstanding the structural loads,namely radial compressive forces, imposed on the stent as it supportsthe walls of a vessel. Therefore, a stent must possess adequate radialstrength. Radial strength, which is the ability of a stent to resistradial compressive forces, is due to strength and rigidity around acircumferential direction of the stent. Radial strength and rigidity,therefore, may also be described as, hoop or circumferential strengthand rigidity.

Once expanded, the stent must adequately maintain its size and shapethroughout its service life despite the various forces that may come tobear on it, including the cyclic loading induced by the beating heart.For example, a radially directed force may tend to cause a stent torecoil inward. Generally, it is desirable to minimize recoil. Inaddition, the stent must possess sufficient flexibility to allow forcrimping, expansion, and cyclic loading. Longitudinal flexibility isimportant to allow the stent to be maneuvered through a tortuousvascular path and to enable it to conform to a deployment site that maynot be linear or may be subject to flexure. Finally, the stent must bebiocompatible so as not to trigger any adverse vascular responses.

The structure of a stent is typically composed of scaffolding thatincludes a pattern or network of interconnecting structural elementsoften referred to in the art as struts or bar arms. The scaffolding canbe formed from wires, tubes, or sheets of material rolled into acylindrical shape. The scaffolding is designed so that the stent can beradially compressed (to allow crimping) and radially expanded (to allowdeployment). A conventional stent is allowed to expand and contractthrough movement of individual structural elements of a pattern withrespect to each other.

Additionally, a medicated stent may be fabricated by coating the surfaceof either a metallic or polymeric scaffolding with a polymeric carrierthat includes an active or bioactive agent or drug. Polymericscaffolding may also serve as a carrier of an active agent or drug.

Furthermore, it may be desirable for a stent to be biodegradable. Inmany treatment applications, the presence of a stent in a body may benecessary for a limited period of time until its intended function of,for example, maintaining vascular patency and/or drug delivery isaccomplished. Therefore, stents fabricated from biodegradable,bioabsorbable, and/or bioerodable materials such as bioabsorbablepolymers should be configured to completely erode only after theclinical need for them has ended.

Potential problems with polymeric implantable medical devices, such asstents, include insufficient toughness, slow degradation rate, andlimited shelf life due to physical aging and stress relaxation.

SUMMARY OF THE INVENTION

Various embodiments of the present invention include a stent fabricatedat least in part from a polymeric material comprising a branchedbiodegradable polymer, the structure of the branched biodegradablepolymer selected from the group consisting of hyperbranched-likepolymers, comb-like polymers, star polymers, dendrimer-like starpolymers, dendrimers, or any mixture thereof in any proportion.

Further embodiments of the present invention include a stent fabricatedfrom a polymeric material comprising an unbranched biodegradable polymerblended with a branched biodegradable polymer, wherein a majority of thepolymeric material comprises the unbranched polymer.

Additional embodiments of the present invention include an implantablemedical device fabricated from a polymeric material, the polymericmaterial comprising a polymer blend including: a matrix polymer blendedwith star-block copolymers having at least three arms, wherein the armsinclude inner segments and outer segments, the inner segments forming adiscrete phase within a continuous phase, the continuous phase includingthe matrix polymer and the outer segments.

Other embodiments of the present invention include a method offabricating an implantable medical device comprising: forming star-blockcopolymers having at least three arms, wherein the arms include innersegments and outer segments; blending a matrix polymer with thestar-block copolymers, wherein the blend comprises discrete phaseregions dispersed within the continuous phase, the continuous phasecomprising the matrix polymer and the outer segments, the discrete phaseregions comprising the inner segments; and fabricating an implantablemedical device from the blend.

BRIEF DESCRIPTION OF THE DRAWINGS

FIG. 1A depicts a view of a stent.

FIG. 1B depicts a section of a structural element from the stentdepicted in FIG. 1A.

FIG. 2 depicts a schematic close-up view of the section depicted in FIG.1B.

FIG. 3 depicts a star-block copolymer having four arms.

FIG. 4 depicts a schematic close-up view of a discrete polymer phasedispersed within a continuous polymer phase.

FIG. 5 depicts a synthesis scheme of a star-block copolymer.

DETAILED DESCRIPTION OF THE INVENTION

Various embodiments of the present invention include an implantablemedical device fabricated from a polymeric material including branchedstructured polymers. Certain embodiments include an implantable medicaldevice fabricated from a polymer blend of a matrix polymer and astar-block copolymer, which includes a discrete polymer phase within acontinuous phase.

As used herein, an “implantable medical device” includes, but is notlimited to, self-expandable stents, balloon-expandable stents,stent-grafts, other expandable tubular devices for various bodily lumenor orifices, implantable cardiac pacemakers and defibrillators, leadsand electrodes for the preceding, vascular grafts, grafts, artificialheart valves, and cerebrospinal fluid shunts. An implantable medicaldevice can be designed for the localized delivery of a therapeuticagent. A medicated implantable medical device may be constructed bycoating the device or substrate with a coating material containing atherapeutic agent. The substrate of the device may also contain atherapeutic agent.

FIG. 1A depicts a view of a stent 100. In some embodiments, a stent mayinclude a pattern or network of interconnecting structural elements 105.Stent 100 may be formed from a tube (not shown). The pattern ofstructural elements 105 can take on a variety of patterns. Thestructural pattern of the device can be of virtually any design. Theembodiments disclosed herein are not limited to stents or to the stentpattern illustrated in FIG. 1A. The embodiments are easily applicable toother patterns and other devices. The variations in the structure ofpatterns are virtually unlimited. A stent such as stent 100 may befabricated from a tube by forming a pattern with a technique such aslaser cutting or chemical etching.

An implantable medical device can be made partially or completely from abiodegradable, bioabsorbable, biostable polymer, or a combinationthereof. A polymer for use in fabricating an implantable medical devicecan be biostable, bioabsorbable, biodegradable or bioerodable. Biostablerefers to polymers that are not biodegradable. The terms biodegradable,bioabsorbable, and bioerodable are used interchangeably and refer topolymers that are capable of being completely degraded and/or erodedwhen exposed to bodily fluids such as blood and can be graduallyresorbed, absorbed, and/or eliminated by the body. The processes ofbreaking down and absorption of the polymer can be caused by, forexample, hydrolysis and metabolic processes.

Some polymers that may be suitable for implantable medical devices suchas stents, have potential shortcomings. One shortcoming is that polymersmay have inadequate modulus and strength for certain applications. Thestrength to weight ratio of polymers is smaller than that of metals. Tocompensate, a polymeric stent may require significantly thicker strutsthan a metallic stent, which results in an undesirably large profile.

Another potential shortcoming of polymer devices is limited shelf lifedue to physical aging and stress relaxation. These processes occur as aresult of creep, which is gradual deformation that occurs in a polymericconstruct. On the molecular level, creep results from relaxation ofpolymer chains. One way of describing chain relaxation is through aprocess of called reptation. In a reptation model, the movement or pathof the polymer chains is depicted as through a tunnel.

Various embodiments of the present invention reduce or eliminate suchshortcomings. Certain embodiments of the present invention include astent fabricated from a polymeric material including a branchedbiodegradable polymer. In general, a branched polymer corresponds to apolymer with “side chains.” Branched polymers include, for example,hyperbranched-like polymers, comb-like polymers, star polymers,dendrimer-like star polymers, and dendrimers. A star-shaped polymerrefers to a polymer having at least three chains or arms radiatingoutward from a common center. A dendritic polymer is a branched polymerresembling a tree-like structure. A comb structure corresponds to alinear polymer segment or backbone having a plurality of side chainsextending outward from a position along the linear segment. In theembodiments described herein, the various polymer structures include aplurality of hydrolytically degradable functional groups or units.

It is believed that the process of reptation is reduced in polymericmaterials that include branched polymers, which reduces creep of thematerial. Thus, a medical device including branched polymers shouldexperience reduced physical aging and stress relaxation.

Additionally, it is also believed that branched polymers increase thestrength of a polymer material. The chemical connectivity provided bythe branched polymers can increase the strength of the polymericmaterial. The segments of the branched polymers may increase strengthand stability of a polymer by acting as chemical net points, byincreased entanglement, or both. Furthermore, it is expected that as apolymer degrades or absorbs, the degradation of mechanical properties,such as strength, is reduced due to the presence of branched polymers.Thus, a device made from a polymer including branched polymers isexpected to maintain mechanical stability longer as it degrades.

In some embodiments, the branched polymers of the polymeric material canbe homopolymers or copolymers. The copolymers can be random or blockcopolymers. In addition, the polymeric material can include one or moretypes of branched polymers. In some embodiments, the mechanicalproperties or degradation rate of the branched polymer can be controlledor tailored though its chemical composition. In one embodiment, thedegradation rate of a branched copolymer can be increased by having ahigher percentage of a unit that is more hydrolytically active. Forexample, the degradation rate of poly(L-lactide-co-glycolide) (LPLG)branched polymer can be increased by increasing the percentage ofglycolide. In a similar manner, the toughness of a branched polymer canbe controlled through the composition of units that form rubbery orelastomeric segments.

In certain embodiments, all or substantially all of the polymericmaterial of the stent is fabricated from a branched polymer. In otherembodiments, a portion of the polymeric material of the stent includes abranched polymer. In some embodiments, the mechanical or degradationproperties of the polymeric material can be tuned by varying the weightpercent of branched polymers in the polymeric material. The weightpercent of branched polymer in the polymeric material of the stent canbe as high as 0.05 wt %, 1 wt %, 10 wt %, 30 wt %, 50 wt %, 70 wt %, 90wt %, or 95 wt %.

In additional embodiments, the molecular weight of branched polymers canbe used to tailor the mechanical and degradation properties of apolymeric material of a stent. In another embodiment, the molecularweight distribution of branched polymers can be used to controlmechanical and degradation properties. The molecular weight distributioncan be monodisperse, broad, bimodal, or multimodal. Properties of amonodisperse polymer may tend to change rapidly over a short time frame.Alternatively, properties of a polymer with a broad molecular weightdistribution may change more gradually. A polymer with a bimodal ormultimodal distribution may exhibit changes in properties in stages.

In additional embodiments, the chemical composition of branches ofbranched polymer of the polymeric material can be the same or different.In other embodiments, the molecular weight of branches can also bedifferent. Thus, the mechanical and degradation properties of thepolymeric material may be tailored by having branches with differentchemical composition, molecular weight, or both.

Branched polymers are known one of ordinary skill in the art. Forexample, various kinds of branched polymer and synthesis andcharacterization of branched polymers can be found in U.S. Pat. No.6,207,767; U.S. Pat. No. 6,231,960; U.S. Pat. No. 5,399,666; U.S. Pat.No. 5,225,521; U.S. Pat. No. 6,316,590; Lowenhielm et al., Macromol.Chem. Phys, 2004, 205, 1489-1496; Trollsas, M. et al., “LayeredDendritic Block Copolymers,” Angew. Chem., Int. Ed. Engl. 1998, 110,3308; Trollsas, M. et al., “Internal functionalization in hyperbranchedpolyesters,” J. Polym. Sci., Chem. Ed. 1998, 36, 3187; Trollsas M. etal., “Dendrimer-like Starpolymers,” J. Am. Chem. Soc. 1998, 120, 4644;Trollsas, M. et al., “Highly branched block copolymers: Design,synthesis and morphology,” Macromolecules, 1999, 32, 4917; Trollsas, M.et al., “Constitutional isomers of dendrimer-like starpolymers,”Macromolecules, 2000, 33, 6423; Trollsas, M. et al., “Dendritichomopolymers and block copolymers: Tuning the morphology andproperties,” J. Polym. Sci., Chem. Ed. 2004, 42, 1174, Ihre et al.,Macromolecules 1996, 118, 6388; and Johansson et al., J. Polym Sci.,Polym. Chem. 1993, 31, 619.

Branched polymers of the polymeric material can include, but are notlimited to, polylactide, polyglycolide, poly(lactic-co-glycolic acid),poly(ε-caprolactone), poly(trimethylene carbonate), poly(hydroxybutyrate), polydioxanone, poly(orthoesters) poly(ethylene carbonate),poly(propylene carbonate), poly(amides), poly(phosphoesters),poly(phosphazenes), poly(anhydrides) and any blends or copolymersthereof. Branched polymers can also include polyester amides,polypeptides, polyethylene glycol, polyacrylates, polymethacrylates,polypropylene oxides, polysaccharides, and any blends or copolymersthereof.

In some embodiments, a multi-arm star polymer can be used as a viscositymodifier to reduce the viscosity during melt processing of a polymer. Inorder to melt process a biodegradable polymer, the temperature of thepolymer is increased to reduce the viscosity to allow flow of thepolymer. To process high molecular weight polymers that, it may benecessary process at a very high temperatures which can causedegradation of the polymer. For example, high molecular weightpoly(L-lactide) (PLLA) with molecular weight in the range from 100 kD to800 kD is extruded at temperatures between 400° F. to 440° F. Thedegradation of the polymer is accelerated in this temperature range.

It has been observed that multi-arm star copolymers can act as viscositymodifiers in melt processing of a polymer. Progr. Polym. Sci. 29, 2004,183-275. Incorporating a multi-arm star copolymer with PLLA in meltprocessing reduces the viscosity of the polymer melt. As a result, thepolymer can be processed at a lower temperature which reduces the amountof molecular weight degradation of the polymer during processing. Insome embodiments, a multi-arm star copolymer can be blended into apolymer before, during, or after melt processing the polymer for animplantable medical device. In an embodiment, the multi-arm starcopolymer can be composed of the same units as the polymer. In anotherembodiment, the multi-arm star copolymer can be composed of differentunits than the polymer. The multi-arm star copolymer can be less than0.05 wt %, 1 wt %, 2 wt %, 5%, or less than 20 wt % of the blend.

Further embodiments of the present invention can include an implantablemedical device fabricated from a polymer blend having a discrete phasewithin a continuous phase. In some embodiments, the polymer blendincludes a matrix polymer blended with a star-block copolymer having atleast three arms. In an embodiment, the arms include inner core segmentsand outer segments with the inner segments being immiscible with theouter segments and the matrix polymer. The inner segments form adiscrete phase with the continuous phase which includes the matrixpolymer and the outer segments. The star-block copolymer can bedispersed throughout the matrix polymer so that there are a plurality ofdiscrete phase regions within the blend. A majority of the polymer blendincludes the matrix polymer.

These embodiments can address additional shortcomings of polymers forrelating to implantable medical devices. For example, some biodegradablepolymers have a degradation rate that is slower than desired for certainstent treatments. As a result, the degradation time of a stent made fromsuch polymers can be longer than desired. For example, a stent made froma semi-crystalline polymer such as PLLA can have a degradation timebetween about two and three years. In some treatment situations, ashorter degradation time is desirable, for example, less than 6 monthsor a year.

An additional shortcoming of some polymers is that their toughness canbe lower than desired, in particular, for use in stent applications. Asindicated above, it is important for a stent to have high radialstrength and stiffness so that it can support a lumen. Some crystallineor semi-crystalline polymers that are glassy or have a Tg above bodytemperature are particularly attractive as stent materials due to theirstrength and stiffness. Some of these polymers, that may be suitable forimplantable medical devices such as stents, have potential shortcomings.One shortcoming of such polymers is that their toughness can be lowerthan desired, in particular, for use in stent applications. For example,polymers such as PLLA are stiff and strong, but tend to be brittle underphysiological conditions. Physiological conditions refer to conditionsthat an implant is exposed to within a human body. Physiologicalconditions include, but are limited to, human body temperature,approximately 37° C. These polymers can exhibit a brittle fracturemechanism at these conditions in which there is little or no plasticdeformation prior to failure. As a result, a stent fabricated from suchpolymers can have insufficient toughness for the range of use of astent.

One way to increase fracture toughness of a matrix polymer is to blendit with a polymer having a higher or relatively high fracture toughnessunder physiological conditions, for example, a rubbery polymer orelastomer. The higher fracture toughness polymer should also beimmiscible with the matrix polymer so that it forms a discrete ordispersed phase within the matrix polymer phase. However, the discreteor dispersed phase should be interfacially compatible with the matrixphase to reduce or eliminate the formation of voids at the interface ofthe phases when the polymer blend is under stress, for example, when astent is expanded. The fracture toughness of a device is increased sincethe discrete phase can absorb energy arising from stress imparted to adevice. To ensure good energy transfer between interfaces of the phases,it is important that there be sufficient bonding or adhesion between thephases. See, Y. Wang, etc. Journal of Polymer Science Part A: PolymerChemistry, 39, 2001, 2755-2766.

In some embodiments, the matrix polymer has a high rigidity and arelatively low fracture toughness at physiological conditions. Suchpolymers may be selected as a matrix polymer for stent applicationssince such rigid polymers can support the walls of a vessel. Thediscrete phase inner segment can have a higher fracture toughness atphysiological conditions. The discrete phase inner segments tend toincrease the toughness of the polymer blend. The outer segments improveadhesion between the continuous and discrete phases to facilitate energytransfer between the phases.

FIG. 1B depicts a section of a segment 110 of strut 105 from the stentdepicted in FIG. 1A. FIG. 2 depicts a microscopic schematic view of aportion 140 of segment 110 of a strut as depicted in FIG. 1B. Portion140 includes a plurality of discrete phase regions 200 dispersed withina continuous phase 210.

FIG. 3 depicts a star-block copolymer 172 having four arms 174. Arms 174have inner segments 176 (shown as broken lines) and outer segments 178.Inner segments 176 are discrete phase blocks and outer segments 178 arecontinuous phase blocks.

FIG. 4 depicts a schematic close-up view of section 250 of FIG. 2 of adiscrete phase region 200 and the interface between discrete phaseregion 200 and continuous polymer phase 210. Section 250 includes astar-block copolymer with inner core segments 310 and outer segments320. Line 330 delineates an approximate boundary between discrete phaseregion 200 and continuous phase 210. L_(D) is a characteristic dimensionof discrete phase region 200. For clarity, matrix polymer segments arenot shown in continuous phase 200.

It is believed that when a device is placed under stress, the discretephase tends to absorb energy when a fracture starts to propagate througha structural element. Crack propagation through the continuous phase maythen be reduced or inhibited. As a result, fracture toughness of thepolymer blend, and thus, the implantable medical device tends to beincreased. The outer segments anchor the discrete phase regions withinthe matrix polymer, increasing the adhesion between the discrete phaseand the continuous phase. Thus, the outer segments facilitate energytransfer between interfaces of the phases. Without the anchoring oradhesion provided by the outer segments, a propagating crack may goaround the discrete phase, reducing the effectiveness of the discretephase in absorbing energy imparted to a device.

Generally, it is desirable for the discrete phase regions to beuniformly or substantially uniformly dispersed throughout the polymermatrix to facilitate the increase in toughness. The more dispersed thediscrete phase regions, the greater is the increase in toughness.Additionally, the increase in toughness is related to the size of thediscrete phase. Both the degree of dispersion and discrete phase sizecan be controlled by the length or molecular weight of the discretephase inner segments. The characteristic length of a discrete phase canbe 1 nm to 100 nm, 100 nm to 500 nm, 500 nm to 1,000 nm, 1000 nm to10,000 nm, or greater than 10,000 nm. The molecular weight of the innersegments can be adjusted to obtain a desired characteristic length. Itcan be 10-50 kD, 50-100 kD, or higher than 100 kD.

In general, the outer segments can be selected so that they are misciblewith the matrix polymer. In some embodiments, the outer segments can bethe same chemical composition as the matrix polymer. For example, apolymer blend with a PLLA matrix polymer can have PLLA outer segments.In some embodiments, the matrix polymer can be a copolymer having a highpercentage of L-lactide units, for example, the L-lactide copolymer canhave at least 80 weight percent of L-lactide units.

In some embodiments, the inner segments of the star-block copolymerinclude units that are form polymers having a higher fracture toughnessat physiological conditions than a rigid matrix polymer, such as PLLA.The discrete phase inner segments can form a discrete phase that is moreflexible and has a lower modulus than the matrix polymer of thecontinuous phase. The matrix polymer can be selected to have a Tg abovebody temperature, so that the matrix polymer remains rigid afterimplantation. Generally, the discrete phase inner segments may beselected that have a Tg below body temperature. In one embodiment, thediscrete phase segments of the star-block polymer can be a rubbery orelastomeric polymer. An “elastomeric” or “rubbery” polymer refers to apolymer that exhibits elastic deformation though all or most of a rangeof deformation. In some embodiments, the discrete phase can besubstantially or completely amorphous.

Biodegradable polymers having a relatively high fracture toughness atbody temperature include, but are not limited to, polycaprolactone(PCL), poly(tetramethyl carbonate) (PTMC), poly(4-hydroxy butyrate), andpolydioxanone. Thus, some embodiments of the discrete phase innersegments of the star-block polymer can include caprolactone (CL),tetramethyl carbonate (TMC), 4-hydroxy butyrate, dioxanone units, or acombination thereof.

In one embodiment, a polymer blend can have a PLLA matrix polymer withP(CL-co-TMC)-b-PLLA star-block copolymer dispersed within the PLLAmatrix. The discrete phase inner segment is P(CL-co-TMC) and the outersegments are PLLA. The PLLA outer segments of the star-block copolymerfor a continuous matrix phase. The PLLA outer segment binds the discretephase with the continuous phase, facilitating the increase in thefracture toughness provided to the polymer blend. In exemplaryembodiments, the polymer blend can include about 1-30 wt %, or morenarrowly, 5-20 wt % of a star-block copolymer and about 75-95 wt % ofmatrix polymer.

Furthermore, a device fabricated from embodiments of the polymer blendscan address issues relating to the degradation rate of polymer devices.As indicated above, a matrix polymer, such as PLLA, can have adegradation rate that is slower than desired for certain stenttreatments. The slow degradation rate is due at least in part to thecrystallinity of a matrix polymer. In some embodiments, the discretephase inner segments of the star-block copolymer can be faster degradingthat the matrix polymer. The faster degradation can be due at least inpart to the amorphous structure of the discrete phase since thediffusion rate of fluids through an amorphous structure is generallyfaster than through a crystalline structure. The faster degrading innersegments increase water penetration and content in the discrete phaseand in the continuous phase. The increased water penetration and contentcauses an increase in the degradation rate of the blend, and thus, thedevice.

In additional embodiments, the star-block copolymer can include units inthe discrete phase inner segments with characteristics that tend toincrease the degradation rate of the blend. For example, the discretephase inner segments can include units that are more hydrophilic thanthe matrix polymer. The discrete phase inner segments can also haveunits that are more hydrolytically active than the matrix polymer. Thesetwo characteristics increase the moisture content of the polymer blendwhich increases the degradation rate of the blend. Additionally, thediscrete phase inner segments can also have units that have acidic andhydrophilic degradation products. Since the rate of the hydrolysisreaction tends to increase as the pH decreases, acidic degradationproducts can increase the degradation rate of the blend and the device.Glycolide (GA) units, for example, have acidic degradation productswhich can increase the degradation rate of a polymer blend when includedin a discrete phase inner segment.

In some embodiments, the discrete phase inner segments can include unitsthat increase the fracture toughness (toughness-enhancing units) of thepolymer blend and units that have one or more of the characteristicsthat increase degradation rate mentioned above (fast degrading units).In an exemplary embodiment, the discrete phase inner segments caninclude both CL and GA units. In particular, the discrete phase innersegments can be poly(glycolide-co-ε-caprolactone) (P(GA-co-CL)).P(GA-co-CL) discrete phase inner segments can have alternating or randomGA and CL units.

An exemplary star-block copolymer for blending with PLLA can includePLLA-b-P(CL-co-GA). The faster degrading GA units can increase thedegradation rate of the polymer blend by increasing the equilibriumwater content and penetration into the structural element. Degradationof GA units further increases the degradation rate due to the acidic andhydrophilic degradation products.

In some embodiments, the flexibility and degradation rate of thediscrete phase inner segments can be adjusted by the ratio of fastdegrading and toughness-enhancing units. As the ratio of CL, forexample, increases in P(GA-co-CL) segments, the star-block copolymerbecomes more flexible and tougher. The Tg of the discrete phase innersegments can be tuned to a desired value by adjusting the ratio ofcomponent monomers. For example, the Tg of the discrete phase may beengineered to be less than a body temperature to provide a more flexiblediscrete phase under physiological conditions. Additionally, thedegradation rate of the discrete phase inner segments, and thus theblend, can be increased by increasing the fraction of GA in the discretephase inner segments. In exemplary embodiments, the P(GA-co-CL) segmentscan have up to 1 wt %, 5 wt %, 20 wt %, 50 wt %, 70 wt %, 80 wt %, or 90wt % GA units.

In an exemplary embodiment, a polymer blend can have a PLLA matrixpolymer with P(GA-co-CL)-b-PLLA star-block copolymer dispersed withinthe PLLA matrix. The discrete phase inner segments are P(GA-co-CL) andthe outer segments are PLLA. The PLLA outer segments of the star-blockcopolymer phase separate into the PLLA matrix of the continuous matrixphase. The PLLA outer segment binds the discrete phase with thecontinuous phase, facilitating the increase in the fracture toughnessprovided to the polymer blend. In exemplary embodiments, the polymerblend can include about 1-30 wt %, or more narrowly, 5-20 wt % of astar-block copolymer and about 75-95 wt % of matrix polymer.

In further embodiments, the matrix polymer can be a copolymer. In someembodiments, a matrix copolymer can be composed of a primary functionalgroup and at least one additional secondary functional group. Thecopolymer matrix may be a random copolymer including the primaryfunctional group and at least one additional secondary functional group.In an embodiment, the copolymer with at least one secondary functionalgroup can have a higher degradation rate than a homopolymer composed ofthe primary functional group. A secondary functional group can have agreater affinity for water or be more hydrolytically active than thesecondary functional group. The secondary functional group can haveacidic and hydrophilic degradation products that enhance the degradationof the matrix polymer and polymer blend. Additionally, a copolymermatrix may have lower crystallinity, which also tends to increasedegradation rate. In some exemplary embodiments, the weight percent ofthe secondary functional group in the copolymer can have up to 1%, 5%,10%, 15%, 30%, 40%, or, at least about 50%. In some embodiments, theweight percent of the secondary function group can be greater than 50%.

In an exemplary embodiment, the matrix copolymer can bepoly(L-lactide-co-glycolide) (LPLG). The primary functional group can beL-lactide and the secondary functional group can be GA. The weightpercent of the GA in the copolymer can be up to 1%, 5%, 10%, 15%, 30%,40%, or at least about 50%. In certain exemplary embodiments, the weightpercent of the GA group can be adjusted so that the degradation time ofa stent, can be less than 18 months, 12 months, 8 months, 5 months, 3months, or more narrowly, less than 3 months.

Additionally, the outer segments of the star-block copolymer can beselected so that the outer segments are miscible with the matrixcopolymer. In one embodiment, the outer segment can have the samechemical composition as the matrix copolymer. In another embodiment, theouter segment can have a composition different from the matrixcopolymer, but close enough so that the outer segment is miscible withthe matrix polymer. In another embodiment, the outer segments can have acomposition different from the matrix polymer with the outer segmentsbeing miscible with the matrix polymer.

In another exemplary embodiment, a polymer blend can have a LPLG matrixpolymer with P(CL-co-TMC)-b-LPLG star-block copolymer dispersed withinthe LPLG matrix. The discrete phase inner segments are P(CL-co-TMC) andthe outer segments are LPLG. The LPLG outer segments of the star-blockcopolymer phase separate into the LPLG matrix of the continuous matrixphase. The LPLG outer segment binds the discrete phase with thecontinuous phase, facilitating the increase in the fracture toughnessprovided to the polymer blend. In exemplary embodiments, the polymerblend can include about 1-30 wt %, or more narrowly, 5-20 wt % of astar-block copolymer and about 75-95 wt % of matrix polymer.

In a further exemplary embodiment, a polymer blend can have an LPLGmatrix polymer with P(GA-co-CL)-b-LPLG star-block copolymer dispersedwithin the LPLG matrix. The discrete phase inner segments areP(GA-co-CL) and the outer segments are LPLG.

Biodegradable multi-arm star-block copolymers can be synthesized throughring opening polymerization. J. Biomater. Sci. Polymer Edn., Vol. 17,2006, 615-630. In some embodiments, a star-block copolymer, such asP(CL-co-TMC)-b-PLLA, P(GA-co-CL)-b-PLLA, P(CL-co-TMC)-b-LPLG, orP(GA-co-CL)-b-LPLG, can be formed by solution-based polymerization.Other methods used to form the star-block copolymers are also possible,such as, without limitation, melt phase polymerization. Insolution-based polymerization, all the reactive components involved inthe polymerization reaction are dissolved in a solvent.

To prepare P(CL-co-TMC)-b-PLLA star-block copolymer, a precursorP(CL-co-TMC) star copolymer may be prepared first by solutionpolymerization. The P(CL-co-TMC) star copolymer is then employed as amacro-initiator to initiate the polymerization of L-lactide monomers toform the PLLA outer segments. This scheme is illustrated in FIG. 5.Specifically, P(CL-co-TMC) star copolymer is formed first by mixingglycerol, CL units, and TMC units with a solvent to form a solution. Inthe solution, the glycerol, CL, and TMC units react to form a three armP(GA-co-CL) star copolymer. L-lactide monomers are added to the solutionor another solution containing the formed P(CL-co-TMC) star copolymer.The L-lactide monomers react with P(CL-co-TMC) star copolymer to formP(CL-co-TMC)-b-PLLA star-block copolymer.

To prepare P(GA-co-CL)-b-PLLA star-block copolymer, precursorP(GA-co-CL) star copolymer is formed first in a solution containing asolvent with GA units, CL units, and pentaerythritol. L-lactide monomersare then added to the solution to react with P(GA-co-CL) star copolymerto form P(GA-co-CL)-b-PLLA star block copolymer.

To prepare P(CL-co-TMC)-b-LPLG star-block copolymer, precursorP(CL-co-TMC) star copolymer is formed first in a solution containing asolvent with CL units, TMC units, and glycerol. L-lactide and GA unitsare then added to the solution to react with P(CL-co-TMC) star copolymerto form P(CL-co-TMC)-b-LPLG star-block copolymer.

The solvent(s) for forming the outer segments can be selected so thatthe star copolymer precursor is soluble in the solvent(s) to enable theprecursor copolymer to copolymerize with outer segment units.

In other embodiments, star-block copolymers can be formed by reactingprecursor star copolymers swollen with a solvent that contain outersegment units. The precursor star copolymer is swollen by a solventafter it is formed so that it can react with outer segment units. One ofskill in the art can select a solvent that swells but does not dissolvethe precursor star copolymer.

In one embodiment, the solvent for use in synthesizing the copolymer isdevoid of alcohol functional groups. Such alcohol groups may act asinitiators for chain growth in the polymer. Solvents used to synthesizethe star-block copolymer include, but are not limited to, chloroform,toluene, xylene, and cyclohexane.

In some embodiments, the polymer blend of the matrix polymer and thestar-block copolymer can be formed by solution blending, melt blending,or a combination thereof. The matrix polymer can be co-extruded with thepolymer blend. The extruded polymer blend may be formed into a polymerconstruct, such as a tube or sheet which can be rolled or bonded to forma construct such as a tube. An implantable medical device may then befabricated from the construct. For example, a stent can be fabricatedfrom a tube by laser machining a pattern in to the tube. In anotherembodiment, a polymer construct may be formed from the polymer blendusing an injection molding apparatus.

In general, representative examples of polymers that may be used inembodiments of the present invention include, but are not limited to,poly(N-acetylglucosamine) (Chitin), Chitosan, poly(hydroxyvalerate),poly(lactide-co-glycolide), poly(hydroxybutyrate),poly(hydroxybutyrate-co-valerate), polyorthoester, polyanhydride,poly(glycolic acid), poly(glycolide), poly(L-lactic acid),poly(L-lactide), poly(D,L-lactic acid), poly(L-lactide-co-glycolide);poly(D,L-lactide), poly(caprolactone), poly(trimethylene carbonate),polyethylene amide, polyethylene acrylate, poly(glycolicacid-co-trimethylene carbonate), co-poly(ether-esters) (e.g. PEO/PLA),polyphosphazenes, biomolecules (such as fibrin, fibrinogen, cellulose,starch, collagen and hyaluronic acid), polyurethanes, silicones,polyesters, polyolefins, polyisobutylene and ethylene-alphaolefincopolymers, acrylic polymers and copolymers other than polyacrylates,vinyl halide polymers and copolymers (such as polyvinyl chloride),polyvinyl ethers (such as polyvinyl methyl ether), polyvinylidenehalides (such as polyvinylidene chloride), polyacrylonitrile, polyvinylketones, polyvinyl aromatics (such as polystyrene), polyvinyl esters(such as polyvinyl acetate), acrylonitrile-styrene copolymers, ABSresins, polyamides (such as Nylon 66 and polycaprolactam),polycarbonates, polyoxymethylenes, polyimides, polyethers,polyurethanes, rayon, rayon-triacetate, cellulose, cellulose acetate,cellulose butyrate, cellulose acetate butyrate, cellophane, cellulosenitrate, cellulose propionate, cellulose ethers, and carboxymethylcellulose.

Additional representative examples of polymers that may be especiallywell suited for use in embodiments of the present invention includeethylene vinyl alcohol copolymer (commonly known by the generic nameEVOH or by the trade name EVAL), poly(butyl methacrylate),poly(vinylidene fluoride-co-hexafluororpropene) (e.g., SOLEF 21508,available from Solvay Solexis PVDF, Thorofare, N.J.), polyvinylidenefluoride (otherwise known as KYNAR, available from ATOFINA Chemicals,Philadelphia, Pa.), ethylene-vinyl acetate copolymers, and polyethyleneglycol. For the purposes of the present invention, the following termsand definitions apply:

For the purposes of the present invention, the following terms anddefinitions apply:

The “glass transition temperature,” Tg, is the temperature at which theamorphous domains of a polymer change from a brittle vitreous state to asolid deformable, ductile, or rubbery state at atmospheric pressure. Inother words, the Tg corresponds to the temperature where the onset ofsegmental motion in the chains of the polymer occurs. When an amorphousor semicrystalline polymer is exposed to an increasing temperature, thecoefficient of expansion and the heat capacity of the polymer bothincrease as the temperature is raised, indicating increased molecularmotion. As the temperature is raised the actual molecular volume in thesample remains constant, and so a higher coefficient of expansion pointsto an increase in free volume associated with the system and thereforeincreased freedom for the molecules to move. The increasing heatcapacity corresponds to an increase in heat dissipation throughmovement. Tg of a given polymer can be dependent on the heating rate andcan be influenced by the thermal history of the polymer. Furthermore,the chemical structure of the polymer heavily influences the glasstransition.

“Stress” refers to force per unit area, as in the force acting through asmall area within a plane. Stress can be divided into components, normaland parallel to the plane, called normal stress and shear stress,respectively. True stress denotes the stress where force and area aremeasured at the same time. Conventional stress, as applied to tensionand compression tests, is force divided by the original gauge length.

“Strength” refers to the maximum stress along an axis which a materialwill withstand prior to fracture. The ultimate strength is calculatedfrom the maximum load applied during the test divided by the originalcross-sectional area.

“Modulus” may be defined as the ratio of a component of stress or forceper unit area applied to a material divided by the strain along an axisof applied force that results from the applied force taken at very lowstrain where the stress-strain curve is linear. For example, a materialhas both a tensile and a compressive modulus. A material with arelatively high modulus tends to be stiff or rigid. Conversely, amaterial with a relatively low modulus tends to be flexible. The modulusof a material depends on the molecular composition and structure,temperature of the material, amount of deformation, and the strain rateor rate of deformation. For example, below its Tg, a polymer can bebrittle with a high modulus. As the temperature of a polymer isincreased from below to above its Tg, its modulus decreases byapproximately 5 orders of magnitude.

“Strain” refers to the amount of elongation or compression that occursin a material at a given stress or load.

“Elongation” may be defined as the increase in length in a materialwhich occurs when subjected to stress. It is typically expressed as apercentage of the original length.

“Toughness” is the amount of energy absorbed prior to fracture, orequivalently, the amount of work required to fracture a material. Onemeasure of toughness is the area under a stress-strain curve from zerostrain to the strain at fracture. Thus, a brittle material tends to havea relatively low toughness.

“Solvent” is defined as a substance capable of dissolving or dispersingone or more other substances or capable of at least partially dissolvingor dispersing the substance(s) to form a uniformly dispersed solution atthe molecular- or ionic-size level at a selected temperature andpressure. The solvent should be capable of dissolving at least 0.1 mg ofthe polymer in 1 ml of the solvent, and more narrowly 0.5 mg in 1 ml atthe selected temperature and pressure, for example, ambient temperatureand ambient pressure.

EXAMPLES

The examples set forth below are for illustrative purposes only and arein no way meant to limit the invention. The following examples are givento aid in understanding the invention, but it is to be understood thatthe invention is not limited to the particular materials or proceduresof examples.

Example 1

The following prophetic example illustrates the synthesis of a multi-armstar copolymer: P(CL-co-TMC)-b-PLLA. In this example the following areused: CL, TMC, and L-lactide (LLA) as monomers; stannous octoate ascatalyst; propane-1,2,3-triol (glycerol) as initiator; and xylene assolvent. The proposed synthesis is as follows:

Step 1: One 2-Liter (L) reactor with a mechanical stirring rod is placedin a sealed glove box filled with high purity nitrogen. The reactor ispreheated to 120° C. for 1 h and purged with high purity nitrogen toremove the moisture and oxygen.

Step 2: A mixture of 100 g CL, 100 g TMC, 92 mg glycerol, 500 mL xylene,and 704 mg stannous octoate is added into the reactor. The solution inthe reactor is then stirred at 120° C. for between 70 h and 120 h.

Step 3: 100 g LLA and 280 mg additional catalyst is then added into thereactor. The mixture is stirred at 120° C. for up to 70 h.

Step 4: Once the polymerization is finished, 1 L CHC1₃ is added intoreactor to dilute the final product. Then the final product isprecipitated into 4-L methanol and dried in vacuum at 80° C. untilconstant weight is achieved.

Example 2

The following prophetic example illustrates preparation of a blend ofthe multi-arm copolymer synthesized in Example 1 and PLLA andpreparation of a stent from the blend:

Step 1: Break P(CL-co-TMC)-b-PLLA star copolymer obtained in Example 1into small pieces in a blender or a cryomiller.

Step 2: Mix PLLA and star copolymer (100:10) through solution blendingor mechanical blending.

Step 3: Extrude PLLA/star copolymer mixture through a signal/twin screwextruder at a temperature to minimize the degradation of PLLA.

Step 4: Prepare stent from extruding tubing.

Example 3

The following prophetic example illustrates the synthesis of a multi-armstar copolymer: P(GA-co-CL)-b-PLLA. In this example the following areused: CL, GA, and LLA as monomers; stannous octoate as catalyst;pentaerythritol as initiator; and xylene as solvent. The proposedsynthesis is as follows:

Step 1: 30 g GA, 20 g CL, 0.035 g pentaerythritol, and 100 ml xylene areadded into a reactor free of moisture and oxygen.

Step 2: 100 mg stannous octoate are added after the temperature hasincreased to 100° C. The solution will become very viscous.

Step 3: Approximately 24 h later, 25 g LLA, and 0.14 mL catalyst areadded.

Step 4: Approximately 96 h later, the final product can be precipitatedinto methanol and dried in a vacuum oven overnight.

Example 4

The following prophetic example illustrates the synthesis of a multi-armstar copolymer: P(CL-co-TMC)-b-LPLG. In this example the following areused: CL, GA, TMC, and LLA as monomers; stannous octoate as catalyst;glycerol as initiator; and xylene as solvent. The proposed synthesis isas follows:

Step 1: 100 g CL, 100 g TMC, 92 mg glycerol, 500 mL xylene are addedinto a reactor free of moisture and oxygen.

Step 2: 704 mg stannous octoate are added after the temperature hasincreased to 120° C. The polymerization solution is stirred at 120° C.for 72 h.

Step 3: 95 g LLA, 5 g GA, and 280 mg stannous octoate are added into thereactor.

Step 4: Approximately 48 h later, the final product is precipitated intomethanol and dried in a vacuum oven overnight.

Example 5

The following prophetic example illustrates the synthesis of a multi-armstar copolymer: P(GA-co-CL)-b-LPLG. In this example the following areused: CL, GA, and LLA as monomers; stannous octoate as catalyst;pentaerythritol as initiator; and xylene as solvent. The proposedsynthesis is as follows:

Step 1: 30 g GA, 20 g CL, 0.035 g pentaerythritol, and 100 ml xylene areadded into a reactor free of moisture and oxygen.

Step 2: 100 mg stannous octoate are added after the temperature hasincreased to 100° C. The solution will become very viscous.

Step 3: Approximately 72 h later 23.75 g LLA, 1.25 g GA, and 0.14 mLcatalyst are added.

Step 4: Approximately 48 h later, the final product is precipitated intomethanol and dried in a vacuum oven overnight.

Example 6

The following prophetic example illustrates preparation of a blend ofP(TMC-co-CO)-b-LPLG (Example 4) or P(GA-co-CL)-b-LPLG (Example 5) andLPLG and preparation of a stent from the blend:

Step 1: Break P(CL-co-TMC)-b-LPLG or P(GA-co-CL)-b-LPLG star copolymerinto small pieces and mix with LPLG with 5 wt % GA content in a blender.

Step 2: Extrude the mixture of LPLG/star copolymer (100:10 weight ratio)through signal or twin screw extruder.

Step 3: Radially expand the extruded tubing and cut into stent with alaser.

While particular embodiments of the present invention have been shownand described, it will be obvious to those skilled in the art thatchanges and modifications can be made without departing from thisinvention in its broader aspects. Therefore, the appended claims are toencompass within their scope all such changes and modifications as fallwithin the true spirit and scope of this invention.

What is claimed is:
 1. A stent scaffolding made completely of a branchedbiodegradable polymer, the structure of the branched biodegradablepolymer selected from the group consisting of hyperbranched-likepolymers, dendrimer-like star polymers, dendrimers, or any mixturethereof in any proportion, wherein the branched biodegradable polymer isan aliphatic polyester selected from the group consisting ofpoly(L-lactide), poly(DL-lactide), polyglycolide,poly(lactic-co-glycolic acid), poly(ε-caprolactone), poly(hydroxybutyrate), poly(trimethylene carbonate), polydioxanone, and any blendsor copolymers thereof.
 2. The stent scaffolding of claim 1, wherein thebiodegradable polymer comprises a random copolymer.
 3. The stentscaffolding of claim 1, wherein the biodegradable polymer comprises ablock copolymer.
 4. A stent scaffolding made completely of a branchedbiodegradable polymer, the structure of the branched biodegradablepolymer selected from the group consisting of hyperbranched-likepolymers, dendrimer-like star polymers, dendrimers, or any mixturethereof in any proportion, wherein the branched biodegradable polymer isselected from the group consisting of poly (ester amides), polyethyleneglycol, and any blends or copolymers thereof.
 5. A stent scaffoldingmade completely of a branched biodegradable polymer, the structure ofthe branched biodegradable polymer selected from the group consisting ofhyperbranched-like polymers, dendrimer-like star polymers, dendrimers,or any mixture thereof in any proportion, wherein the branchedbiodegradable polymer is selected from the group consisting ofpolyacrylates, polymethacrylates, polypropylene oxides, polysaccharides,polyamide, and any blends or copolymers thereof.